Classifications

• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
  • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
  • A61L27/02—Inorganic materials
  • A61L27/04—Metals or alloys
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
  • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
  • A61F2/02—Prostheses implantable into the body
  • A61F2/022—Artificial gland structures using bioreactors
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
  • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
  • A61L27/14—Macromolecular materials
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
  • A61M1/3472—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration with treatment of the filtrate
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
  • A61M1/3472—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration with treatment of the filtrate
  • A61M1/3475—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration with treatment of the filtrate with filtrate treatment agent in the same enclosure as the membrane
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
  • A61M1/3472—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration with treatment of the filtrate
  • A61M1/3486—Biological, chemical treatment, e.g. chemical precipitation; treatment by absorbents
  • A61M1/3489—Biological, chemical treatment, e.g. chemical precipitation; treatment by absorbents by biological cells, e.g. bioreactor
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
  • A61M1/3472—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration with treatment of the filtrate
  • A61M1/3493—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration with treatment of the filtrate using treatment agents in suspension
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
  • A61P3/00—Drugs for disorders of the metabolism
  • A61P3/08—Drugs for disorders of the metabolism for glucose homeostasis
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
  • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
  • A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
  • A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
  • A61M1/1678—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes intracorporal

Definitions

• Beta cells the insulin-producing cells of the pancreas, comprise more than 70% of the cell population found in discrete collections of cells in the pancreas which are known as islets of Langerhans .
• Some major effects of insulin are to increase the uptake of glucose by various tissues including muscle and fat and to decrease glucose output by the liver. Either absolute or relative insulin deficiency impairs glucose uptake and increases hepatic glucose output, thereby resulting in the abnormally high blood glucose concentrations characteristic of diabetes mellitus.
• Insulin release from pancreatic islets is controlled by a combination of factors, including the concentration of glucose and other nutrients in the blood, gastrointestinal hormones and neuronal stimuli. In humans, glucose is the principal stimulus for insulin secretion from beta cells.
• Diabetes is generally characterized by an elevated concentration of glucose in the blood and urine. Insulin is administered to a diabetic patient in an effort to control or regulate the concentration of glucose and other nutrients in the blood. The objective of this regimen is to maintain glucose levels close to normal.
• Insulin is administered to a diabetic patient in an effort to control or regulate the concentration of glucose and other nutrients in the blood.
• the objective of this regimen is to maintain glucose levels close to normal.
• One possible reason for the failure of this treatment to prevent the complications associated with diabetes is that daily insulin injections do not mimic the rapid insulin secretory responses of normal islets to physiological demand. Consequently, there has been a great deal of interest in developing a treatment for diabetics which would make it possible to maintain normal blood glucose levels at all times, an objective extremely difficult or impossible to achieve by insulin injections, diet and exercise.
• pancreatic tissue Another approach to treating diabetes is replacement of the malfunctioning organ by transplantation of normal pancreatic tissue.
• transplantation of pancreatic tissue has met with limited success due to problems of tissue typing, donor availability and immune rejection.
• researchers have focused on creating a hybrid artificial pancreas which mimics the organ's physiological response to glucose levels.
• Artificial pancreatic devices containing live islets have been designed to avoid immune rejection. These devices contain a semipermeable membrane which separates the transplanted islets from immunoreactive cells and molecules.
• Matsumura describes an artificial pancreas device which includes a seraipermeable membrane on one side of which onjce-dispersed live pancreatic islets are placed.
• Sun et_al ⁇ (U.S. Patent No. 4,323,457 (1982)) describe another artificial pancreatic device which is a container means through which a hollow fiber of 500 ⁇ m diameter is passed. The container holds pancreatic islets and the fiber is described as having a porosity which allows for passage of substances of molecular weight less than 100,000 Daltons .
• Chick et_al ⁇ (U.S. Patent No. 4,242,459 and No. 4,242,460 (1980)) describe a cell culture device having a generally circular fluid-tight cavity and a semipermeable tube wrapped about itself to form coils.
• Another cell culture device comprises a housing and a stationary spool about which a semipermeable tube is wrapped to form coils.
• pancreatic devices solve the problems associated with diabetes and with implantation of an artificial device into an individual.
• a pancreatic device containing viable islets of Langerhans which can be implanted into a diabetic individual and be effective in controlling blood glucose levels in such a way as to mimic normal physiological response to changing blood glucose concentrations.
• parent Application U.S. Serial No. 07/398,739 discloses one such device, that application does not discuss replacement of islets during , in_vivo use.
• a method and/or pancreatic device in which islets can be removed from the device and replaced with fresh islets at various times during use, for example upon a drop in insulin output.
• the present invention relates to an artificial organ perfusion device, in particular an artificial pancreatic perfusion device which results in the secretion of insulin into the blood of an individual in response to changes in blood glucose concentrations.
• the device employs a hollow fiber for passage of blood through a housing which contains pancreatic islets of Langerhans in an appropriate supporting material and a connecting means for connecting a blood vessel, such as a vein or an artery, to the ends of the hollow fiber to provide continuous flow from the individual , through the device and back into the individual.
• the islets are introduced into the housing suspended in a supporting material which physically distributes and maintains position of the islets about the length of the hollow fiber.
• the supporting material is a substance that is sufficiently viscous to physically support and maintain location of the islets about the fiber but sufficiently fluid to enable removal of the supporting material, with the islets, from the housing.
• the supporting material of this invention renders the device reseedable (i.e. , enables substitution of islets by replacement of the islet suspension or portion thereof).
• the supporting material comprises calcium sodium alginate or similar semi-gel (gel-like) media or matrixes.
• this matrix has a viscosity of about 900 to 1000 centipoises at 37 ⁇ C.
• the supporting material aids maintenance of islets in culture.
• the supporting material preferably includes islet cell culture medium and islet cells to form an islet mixture.
• the islet suspension is prepared from the islet mixture, for introduction into an artificial pancreatic device, by centrifuging to form a culture medium phase and an islet suspension phase.
• the culture medium phase is removed, and the device is seeded with the remaining islet suspension phase.
• Temperature sensitive matrices are employed as the gel-like matrices of the present invention.
• Such temperature sensitive matrices are in a gel-like, fluid physical state above about 45°C and solidify to a semi-solid matrix at temperatures about body temperature (i.e. , less than about 45 ⁇ C) to form a semi-solid matrix within the device.
• body temperature i.e. , less than about 45 ⁇ C
• Such a matrix is introduced into an artificial pancreatic perfusion device at a temperature about 48° - 50°C and allowed to cool to less than about 45"C to form a semi-solid matrix within the device.
• Subsequent softening of the matrix to a gel-like state is accomplished by flushing the device with a solution having temperatures in the range of about 48°C to 50 ⁇ C, or by w «.
• FIG. 1 is a schematic view of an artificial pancreatic perfusion device generally embodying the present invention.
• Figure 2 is a schematic view of another artificial pancreatic perfusion device embodying the present invention and having a coiled housing.
• Figure 3a is a schematic view partially cut away of another embodiment of the present invention having an annular housing.
• Figure 3b is a plan view of the embodiment of Figure 3a.
• Figure 3c is an exploded view of another embodiment having a lightweight annular housing.
• Figure 4 is a graphic representation of insulin producing islet viability in culture in a calcium sodium alginate matrix of the present invention.
• the present invention relates to a device useful for controlling fluctuations in blood glucose levels, as well as to a method of treating such fluctuations, particularly in individuals with diabetes.
• the device includes viable intact pancreatic islets of angerhans , islet fragments, beta cells, or a combination thereof, which sense and respond to blood glucose levels as blood flows through a hollow fiber which selectively allows passage of molecules having a molecular weight of less than about 100,000 Daltons.
• the term hollow fiber is meant to encompass various hollow, tissue compatible materials capable of transporting a medium (i.e. , blood) and having a selected porosity which selectively allows the passage of substances across the material.
• FIG. 1 An artificial pancreatic perfusion device embodying the present invention is illustrated in Figure 1 and generally referenced as 40.
• the device provides a hollow fiber 12 surrounded by islets of Langerhans 14.
• Hollow fiber 12 is a porous membrane with pore size which selectively allows transverse passage of substances having a molecular weight of less than about 100,000 Daltons .
• the pores allow diffusion of glucose and necessary nutrients from the blood through the walls of hollow fiber 12 to islets 14 as the blood flows along the length of the fiber 12.
• the islets 14 generate and secrete insulin, which diffuses from outside of hollow fiber 12 through the walls of the fiber and into the blood flowing therethrough.
• the insulin-containing blood i.e. , blood flowing from the device exits fiber 12 at outlet end 18 to provide the generated insulin to the individual.
• one end of hollow fiber 12 is connected by connecting means to a blood vessel, such as an artery, for receiving blood, and the opposite end of fiber 12 is connected by connecting means to a second blood vessel, such as a vein, for providing insulin-containing blood to the individual.
• a blood vessel such as an artery
• a vein for providing insulin-containing blood to the individual.
• connections other than to an artery and vein are suitable as long as blood or other medium flows through hollow fiber 12 from inlet end 16 to outlet end 18.
• the connecting means can be comprised of any one of various tissue compatible materials such as vascular graft material.
• the ends of the hollow fiber can be connected by connecting means to a single blood vessel, such as an artery or vein.
• hollow fiber 12 is a porous acrylic copolymer membrane of about 100,000 Dalton average porosity, such as the type XM, manufactured by the Amicon Division of W.R. Grace & Co. -Conn.
• the pore sizes selected provide a barrier to protect the xenograph from a host immune reaction.
• a pore size is selected on the basis that the fiber must retain >90% of an IgG solution.
• the islets can be obtained from a variety of mammalian sources, such as canine, bovine, porcine, or human pancreatic tissue, without necessarily requiring immunomodulation of the islets or immune suppression of the recipient.
• the ends of the hollow fiber are connected to a blood vessel or vessels in such a way that the inner diameter of the fiber substantially matches the inner diameter of the blood vessel, to provide smooth and continuous flow of blood.
• a fiber having an inner diameter which substantially matches the inner diameter of the vessel can be employed.
• hollow fiber 12 has a uniform inner diameter of about 4 mm to about 7 mm. Such a diameter is compatible with the inner diameter of an individual's arteries and veins to which ends of fiber 12 are to be connected in i.n_yLvo use of the device. As a result, the potential for clotting at vascular connective junctions is reduced.
• the hollow fiber can have an inner diameter which differs from that of a blood vessel.
• the hollow fiber can be adapted with a connecting means which at one end substantially matches the diameter of the vessel and at an opposite end substantially matches the diameter of the fiber, thus providing smooth and continuous flow of blood from the blood vessel and into the device.
• the connecting means can comprise a butt joint providing a smooth, essentially step free internal transition between the vessel and the fiber 12.
• the butt joint is made using a mandrel which can be either rigid or made of a deformable material.
• the mandrel is placed in the fiber and graft lumen to match the internal diameters .
• a smooth rigid rod can be utilized as a mandrel.
• the rod must have a tapered end that fits tightly into the lumens of both the fiber and graft.
• a deformable material that will expand when compressed can also be used as a mandrel. This can be placed in the lumens of the fiber and graft and expanded. The expanded material will tightly fit the graft and fiber creating a gradual transition between the fiber and graft.
• adhesive can be cast around the mandrel between a slight gap left between the fiber and graft. Upon curing the mandrel can be removed and a smooth internal transition between the fiber and graft will remain.
• the fiber has a wall thickness of 100-200 microns and a length sufficient to provide an inner surface
• 2 area of the hollow fiber can be about 100 cm and the length of the fiber can be about 56 cm, which has been shown to be sufficient to support about 300,000 islets iH_XU££•
• the islets 14 are introduced or seeded into the device in such a manner that the islets are distributed about hollow fiber 12.
• an appropriate supporting material such as a semi-gel matrix or temperature sensitive matrix, that forms a suspension of the islets (referred to as an islet suspension) is used.
• the supporting material can be comprised of various substances which are capable of maintaining islet viability and physically supporting the islets in suspension.
• the semi-gel matrix is sufficiently viscous to physically suspend and support the islets and yet sufficiently fluid to be pipettable (i.e. , removable from and injectable into the device by suitable means such as by vacuum).
• the semi-gel matrix has a viscosity between a liquid and semi-solid.
• the islet suspension can be introduced into the device in a manner such that islets are distributed and maintained about the outside of fiber 12.
• Use of the temperature sensitive matrix described herein means that the islet suspension is removable by suction means such as a syringe or the like. This allows the device to be easily reseeded with fresh islets 14 as necessary or desired. Such reseeding is advantagous in prolonging the operating life of the device.
• a temperature sensitive matrix may be employed which is in a liquified physical state at about 48°C-50 ⁇ C and in a solidified or semi-solid physical state at body temperature (about 37°C), and which fairly easily changes states with a change in temperature.
• a temperature sensitive matrix is described in U.S. Patent No. 5,002,661 as a semi-solid matrix formed from liquified agar. Briefly, a matrix is formed by adding islets to liquified agar. The liquified agar with islets form a liquified islet suspension which is introduced into the device in a manner that distributes the islets about the outside of fiber 12.
• the liquified islet suspension is allowed to cool to less than about 45°C, which in turn allows the matrix to solidify to form a semi-solid matrix, such that the islets are maintaine distributed and suspended about the outside of fiber 1 .
• the matrix remains in this semi-solid physical state during use in temperatures below about 45°C, for example at body temperature of about 37"C.
• Subsequent softening of the matrix to its liquified gel-like state is then accomplished by flushing a warm (48 ⁇ C- 50°C) saline solution through the device, but external to the islet matrix portion (i.e., about the outside of the fiber 12) .
• the device may then be reseeded with fresh islets 14 as desired.
• the temperature sensitive matrix also allows storage under ⁇ 2_.£i£££ culture conditions (e.g. , 37 ⁇ C) to maintain the islets.
• the islet suspension comprises islet cell culture medium.
• islet mixture is used herein to refer to the supporting material/islet/culture medium mixture.
• islet suspension is used herein to refer to the supporting material/islet mixture without culture medium, although the islet suspension may contain other components, as described below.
• the islet mixture portion is centrifuged to form a culture medium phase and an islet suspension phase.
• the culture medium phase is removed and the remaining islet suspension phase is introduced into the device for use to produce insulin.
• subsequent amounts of islet mixture from culture may be similarly processed and used in the device, each subsequent islet suspension portion being substituted for some or all of the islet suspension in the device.
• Each islet suspension portion or subsequent portion should be in an amount sufficient for the production of a desired amount of insulin by the device.
• the housing can be comprised of plastic (e.g. , polyacrylic) , stainless steel, titanium or other implantable metallic substance.
• the housing can be polycarbonate, polysulfone, polymethyl methacrylate or mixtures thereof.
• the housing must be tissue compatible and sufficiently inflexible to protect hollow fiber 12 and is preferably lightweight.
• extruded plastic housing 42 is generally cylindrical in shape and is as long as hollow fiber 12. Housing 42 coaxially encompasses hollow fiber 12, which lies substantially straight and curveless within housing
• Inner walls of housing 42 form a chamber 34 about the outer surface of fiber 12.
• the islet suspension is distributed circumferentially and longitudinally along the length of hollow fiber 12 in this chamber 34.
• housing 20 is generally tubular in shape and follows the contour of hollow fiber 12 which is, for example, about 22 inches long. More specifically, housing 20 is coaxially positioned about fiber 12 along the length of fiber 12 and housing 20 together with fiber 12 are coiled about a longitudinal axis to provide a space saving compact device 10. In such a configuration, inner walls of housing 20 form a chamber about the outer surface of hollow fiber 12. It is into this chamber that the islet suspension is introduced such that fiber 12 is surrounded along its length by islets 14.
• FIGs 3a and 3b A preferred embodiment of the present invention is illustrated in Figures 3a and 3b and is generally referenced 30.
• Hollow fiber 12 is coiled into one or more loops about a longitudinal axis, and the coiled fiber is enclosed in an annular shaped housing 22.
• each loop formed by hollow fiber 12 within housing 22 may be spaced apart from a preceeding and succeeding loop by spacers 24.
• the spacers 24 ensure a gap 25 between each loop of fiber 12 and ultimately enable the islet suspension to be positioned circum erentially along the length of hollow fiber 12.
• the islet suspension is introduced into annular housing 22 in a manner which substantially fills gaps between loops of hollow fiber 12 as well as areas around the inner and outer curves of each loop, such that the islet suspension and thus islets 14 surround fiber 12 along its length.
• housing 22 includes injection ports 26 and 28 as shown in Figure 3b. These ports aid in the introduction of the islet suspension into the housing in such a manner that it surrounds coiled hollow fiber 12 within the housing 22. In the present invention, the suspension is drawn through one port 26 by negative pressure generated at the other port 28.
• a syringe containing the islet suspension is positioned, as for injection, at port 26.
• Means for drawing air from housing 22, such as a second syringe, is positioned at port 28.
• the drawing means is operated so as to withdraw air from housing 22 through port 28 and thus create a current directed from port 26 through housing 22 and out port 28. Consequently, the negative pressure pulls the islet suspension from the first syringe through port 26 and into housing 22, and toward port 28.
• screens 32 can be attached to cover internal openings 36 of port 28.
• screens 32 comprise a tissue compatible mesh material with apertures sufficient to prevent islets from being withdrawn (i.e. , smaller than the islets) .
• screens with 20-30 micron wide apertures such as of the Nytex brand or similar type can be used.
• Screens 32 are fastened to the inner walls of housing 22 over openings 36 by common methods and means, including tissue compatible epoxies.
• hollow fiber 12 exits the annular shaped housing 22 so that one end 16 of hollow fiber 12 is connected to a blood vessel, such as an artery, in such a manner that blood flows into, through and out of the device.
• a blood vessel such as an artery
• An opposite end 18 of hollow fiber 12 is connected to a second blood vessel, such as a vein, for providing insulin-containing blood to an individual, as described in Figure 1.
• the annular shaped housing 22 may also provide one or more suture sites 38, through which the device 30 is anchored to the individual .
• the annular housing is designed to be particularly lightweight.
• a lightweight annular housing is illustrated in an exploded view in Figure 3c and is described below.
• a bottom half 44 is machined from acrylic with a figure-8 central cavity 68, an inner circumferential groove 54, two bores 56 (preferably 1/16 inch diameter) leading into the circumferential groove 54 and suture sites 64 about the exterior.
• the hollow fiber 12 sits coiled in groove 54 with ends 16 and 18 attached to connecting means, such as vascular grafts 52 for i.2_ ⁇ ivo use °f tne device 60.
• the housing bottom half 44 is shaped to accommodate vascular grafts 52 connected to the fiber ends 16 and 18 to allow these grafts to protrude from the housing.
• a butt joint can be made using a mandrel as described previously to provide a smooth, essentially step free internal transition between the fiber and graft lumen.
• a screen such as the screen 32 described in Figure 3b, can be attached to the wall of groove 54 to cover the opening of bore 56 in the groove to prevent drawing of islets out of the housing during introduction of the islet suspension into the housing.
• a housing top half 46 is machined from acrylic with a figure-8 central cavity 68, openings 58 and an inner circumferential groove which match respectively the figure-8 central cavity 68, bores 56 and inner groove 54 in bottom half 44. Housing top half 46 is welded or otherwise hermetically sealed to bottom half 44 with respective matching parts aligned. Snapped into openings 58 are injection port assemblies 48.
• Each injection port assembly 48 includes a silicon plug 50 inside a cap 62, as is common in the art.
• the port assemblies 48 positioned in openings 58 provide the injection ports or sites for introducing the islet suspension to hollow fiber 12 coiled within the housing inner groove 54. Al ernatively, injection sites could be welded into either the housing top half 46 or bottom half 44.
• a tissue compatible adhesive is applied to where the housing meets the connecting means to ensure a hermetic seal.
• Epoxy of medical grade such as T674 manufactured by Emerson and Cumings , Inc. (Polyfibron Division of W.R. Grace & Co. -Conn.), is preferred. Because of the central cavity, the device 60 with the islet suspension surrounding fiber 12 weighs about 40 grams. Planar covers, of silicon or like material, for the top and bottom sides of the housing cover the figure-8 central cavity and prevent fluid from building up within the cavity during .i ⁇ _vi ro use of the device 60 without adding substantial weight.
• Such covers are attached to the respective outer surfaces of housing top half 46 and bottom half 44 by welding, adhesive or other methods and means common in the art. It is understood that other configurations of the present invention are possible. Such configurations need only ensure the distribution of islets about hollow fiber 12, preferably circumferentially and longitudinally about fiber 12, such that fiber 12 is surrounded along its length by the islets 14. In optimizing the design of a configuration, it is understood that the distance between the islets and hollow fiber 12 needs to be minimized to maximize diffusion of substances, including substances which stimulate insulin secretion, as well as nutrients and oxygen, from the blood to the islets.
• pancreatic islets of Langerhans are isolated from any one of various mammalian pancreatic tissues, for example canine, bovine, porcine, or human.
• the term "islet” or “islets” as used herein includes the constituent cell types within the islet of Langerhans, including beta cells, the actual producers of insulin, intact islets, islet fragments or combinations thereof.
• the procedure for isolating islets from the exocrine tissue of the donor pancreas is described in Example I.
• Islets of Langerhans are suspended in an appropriate supporting material.
• One such supporting material includes liquified agar.
• Additional components, such as collagen and laminin and/or growth factors can be added to the islet suspension.
• collagen and laminin and/or growth factors can be added to the islet suspension.
• approximately 100 ⁇ g/ml of collagen I, approximately 80-100 ⁇ g/ml of collagen IV and approxi- mately 5-10 ⁇ g/ml of laminin can be added to the islet suspension.
• the islet suspension can also contain other cells which enhance islet viability.
• the presence of endo- thelial cells or fibroblasts can create an environment more like that in which islets occur naturally.
• Other cell types which produce growth factors or basement membrane components can be cultured with the islets to enhance growth and viability.
• an endo- thelial cell layer at the graft site can contribute to increased patency of the anastomosis site.
• the invention provides a method for seeding an artificial pancreatic perfusion device with a suspension of islets of Langerhans prior to use of the device.
• the invention also provides a method for reseeding the device with fresh islet suspension on one or multiple occasions following use of the device for insulin production.
• the islet suspension formed of the temperature sensitive matrix at a temperature rendering its gel-like physical state is introduced to the outside of hollow fiber 12 as described previously in conjunction with Figure 3b.
• the matrix solidifies to form a semi-solid matrix which suspends the islets in their respective locations about hollow fiber 12. Upon warming, the matrix becomes sufficiently fluid to enable easy removal and substitution of the islet suspension on further occasions as necessary. For example, reseeding may be indicated after a decrease in insulin production by the device.
• the temperature sensitive matrix suspends the islets about hollow fiber 12 and upon cooling to a temperature of less than about 45 C C forms a semi-solid matrix that supports the islets in a distribution about fiber 12. With subsequent warming of the matrix above about 45"C for a few minutes (i.e. , via warm, 48°C - 50°C, solutions introduced into the chamber about the outside of fiber 12, or warming the environment about the device, or the like) , the matrix returns to a more fluid state which enables easy removal from the device as desired or needed. Further details of the preparation of a temperature sensitive (e.g. , agar) islet suspension are found in Example II. Details of use and reseeding protocol in the case of a temperature sensitive islet suspension are found in Prospective Example A.
• a temperature sensitive e.g. , agar
• Inlet end 16 and outlet end 18 are attached to connecting means, such as vascular graft material, for example polyurethane , polytetrafluorethylene, or
• Preparation of the semi-gel islet suspension, and the seeding and reseeding protocol in a preferred embodiment is as follows. Islets of Langerhans are added to a solution of liquified agar and cell culture medium (hereinafter agar/medium solution) , forming an islet mixture. For use in the seeding or reseeding of the device, the semi-gel form of the islet mixture is centrifuged to form a culture medium phase and an islet suspension phase.
• the culture medium phase is removed and the islet suspension phase is used in one or more portions to seed and/or reseed an artificial pancreatic device of the present invention.
• the islet suspension may be formed directly by adding islets to liquified agar (i.e. , without including cell culture medium) .
• agar/medium solution Another application for the agar/medium solution is the long term maintenance of islets in culture.
• a difficulty encountered in maintaining islets in culture is that they attach to the tissue culture plastic of the chambers in which they are maintained. Once attached they are difficult, if not impossible, to remove from the plastic and use for experiments or perfusion device seeding.
• an islet mixture is formed which suspends the islets as well as provides nutrients to enable the islets to be maintained in culture for extended periods.
• the islet mixture and islet suspension can easily be transferred from vessel to vessel without adversely affecting islet function, by warming to convert the matrix to a semi-gel.
• the islet mixture can be used both to maintain islets in culture and as a basis from which to prepare the islet suspension for the artificial pancreatic perfusion devices described above.
• the islet mixture is formed as described above and maintained in i.n_vi ⁇ tr£ culture.
• a first portion of islet suspension is obtained for use in a device by centrifugation of a first amount of the semi-gel islet mixture and separation of the resulting culture medium-phase from the islet suspension phase.
• the islet suspension phase is injected into and used in the artificial pancreatic perfusion device for the production of insulin for a desired period of time.
• a second amount of the semi-gel islet mixture is subsequently taken from culture and centrifuged to prepare a second portion of islet suspension which is used to reseed the device after removal of all or part of the first portion of islet suspension, as described above.
• Other amounts of the islet mixture are similarly taken from culture and centrifuged to prepare further islet suspension portions used to reseed the device on multiple occasions for the continued production of insulin by the device.
• the islet mixture and islet suspension of this invention may be used in a variety of in_vi.tro or in_vi ⁇ vo devices which require a supporting material to distribute and maintain the position of islets, and for which it may be desired to replace all or a portion of the islet suspension following a period of use.
• the cell culture medium is required to maintain the islets in culture prior to placing them in an i ⁇ n vivo or _! _Y.i£££ device, but that cell culture medium is not required where the isolated islets will be used immediately in a device which will maintain their viability. After the cells are placed in a device, islet viability is maintained by cell culture medium or blood being perfused through the device.
• Islets of Langerhans were obtained from pancreata of donor animals (e.g. ; dog, cattle, pig) . Islets of Langerhans were isolated and purified by a modification of published procedures, Moskalewski, S. , Gen ⁇ _C ⁇ m ⁇ _Endo ⁇ , 5:342 (1965); Lacy P.E. and M. Kostianovsky , Diabetes, 16_:35 (1967); Lacy, P.E. et H ⁇ . ⁇ Di 2 tes, 31_£Su__l ⁇ _4i: 109 (1982) .
• pancreas was infused via the pancreatic duct with a suspension of collagenase which digested connective tissue and disrupted the integrity of the gland.
• the gland was further dissociated by shaking with marbles until tissue fragments were reduced to a size of less than 500 microns diameter. This disassociation procedure released islets from the exocrine tissue that surrounded them. Islets were then separated from non-islet tissue by centrifugation on a discontinuous
• the 2% (wt/vol) agar gel (Sterile Bacto-Agar Difco) was liquified by heating.
• the volume of suspension necessary for embedding in a device was one-half of the cell compartment volume (e.g. , cell chamber volume of 6 ml) .
• An islet pellet was obtained by collecting isolated islets and centrifuging. This pellet was brought up to a volume of 3 ml (H of cell chamber volume of 6 ml) with the addition of 2X media M199/EBSS (media 199; Earls Balanced Salt Solution).
• 2X media M199/EBSS media 199; Earls Balanced Salt Solution
• additives e.g. , collagen, laminin, growth factors
• IX media 100 ⁇ g/ml collagen IV 5 ⁇ g/ml laminin
• the islet suspension was seeded through injection ports as in Figures 3b and 3c, or distributed by some other means as in Figures l-3a.
• the liquified agar suspension was applied to the device and then placed on ice for approximately 10-15 minutes to effectively gel the agar, prior to implantation, to form a martix in which the islets were suspended.
• Islets are seeded into a device as described in Figures 3b and 3c following the embedding procedure in Example II above.
• the seeded device is then ready for implantation into a desired subject.
• the device is reseeded with the liquified agar islet suspension described in Example II.
• the reseeding procedure includes flushing the device for a few minutes with a saline or balanced salt solution warmed to a temperature of about 48 ⁇ C - 50°C. Such flushing essentially warms the islet suspension in the device to the melting point of agar (about 45 ⁇ C) .
• the islet suspension in the device changes from a semi-solid to a semi-gel, which enables removal of this portion of the islet suspension. Removal is by suction, such as by a syringe, through injection ports 26, 28 shown in Figures 3b and 3c. The substituting portion of the temperature sensitive islet suspension is then introduced through the injection ports as previously described. Other intermediate steps may be taken between removal of the initial portion of islet suspension and introduction of the substituting portion, such as flushing or other cleaning procedures.

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• 1991
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